Optical trapping employs a tightly focused laser beam to trap and manipulate particles ranging from tens of nanometres to tens of micrometres in diameter in 3D space1. The technique, also referred to as optical tweezing, enables forces in the range of a few hundred pN to be generated with a resolution down to 50 fN in contemporary systems2,3. The combination of these features results in a potent and reliable approach for the contactless manipulation of particles with high spatial and temporal precision across a range of length scales; properties that are ideal for probing biological systems4. To this end, optical traps have been used to manipulate individual cells, viruses and organelles1,5,6,7, to extract and sample materials from plasma membranes8, and to elucidate the biophysics  of protein folding9, molecular motors10, and ribosome translation one codon at a time11. Further, optical traps have also been used to study the surface tension, elasticity and bending modulus of soft matter systems such as biological membranes by generating long tether-like nanotubes12. Optical traps have more recently been used to construct 2D and 3D model membrane architectures, including networks of droplet interface bilayers13,14 and giant unilamellar vesicles (GUVs)15, which can be positioned into contact and fused together to deliver material payloads via lipid-conjugated gold nanoparticles15,16. This new frontier in the use of optical traps is leading the technique to be considered as a powerful tool for bottom-up synthetic biologists, enabling increasingly complex cell and tissue-mimetic architectures to be engineered on-demand. These studies, however, have all involved gross manipulation of entire membrane structures in space.

Despite this progress, to date, there have been no reports of direct optical trapping of laterally segregated domains within lipid bilayers, i.e., where the membrane itself acts as the 2D fabric in which embedded structures are manipulated. In this case, membrane domains are defined as coexisting phase separated regions in lipid membranes17. Achieving this will pave the way for optical traps to be used as tools to probe domain biophysics and have implications for the design and construction of membrane microsystems with user-defined membrane patterning.

Lipid domains, which are thought to be linked to cell membrane rafts18,19, arise due to a fundamental property of certain lipids to transition between a gel phase (Lβ) and a liquid phase (Lα) at a defined melting temperature (Tm). These phases can coexist at certain temperatures in dual component bilayers made up of high and low Tm lipids. When cholesterol is added, phase-separated liquid disordered (Ld) and liquid ordered (Lo) domains can be formed. The system can be reverted back and forth from a phase separated to a mixed state by performing heating cycles past the characteristic miscibility temperature (Tmisc)20.

There is mounting evidence to suggest that this lateral organisation plays a key role in biological membranes, with lipid rafts thought to be involved in a range of cellular activity from signalling and trafficking, to providing a mechanical support for the anchoring of membrane proteins18,19,21,22,23,24. Yet due to the lack of experimental data obtained in-vivo, the biological significance of lipid domains remains a contentious topic.

There have been extensive efforts at using model systems to study membrane domains, using systems such as supported lipid bilayers25, planar lipid membranes26,27, GUVs28,29, and droplet-hydrogel bilayers30. The advantage of using model systems in this context is that the size, composition, degree of compartmentalisation, and level of asymmetry of the assembled membrane can be carefully controlled by the investigator, especially when microfluidic methods are employed31. This has led to advances in our understanding of fundamental membrane behaviour, and of the properties that govern their cellular functions. However, methods to manipulate individual domains formed both in native and model bilayers do not yet exist, which partly explains why their biological significance is still poorly understood.

Indirect domain motion arising from thermal gradients32,33, electric fields34, and fluid flows35,36 have been elegantly demonstrated, but these methods lack the spatiotemporal control afforded by optical traps. Manipulation of non-phospholipid domains on a langmuir monolayer (water/air interface), using optical traps via silica beads as ‘handles’ localised in the phase coexistence region37,38,39, and via director structures and defects in liquid crystals40 has also been demonstrated.

However, the ability to directly manipulate biologically relevant lipid domains within a bilayer system has yet to be realised. Manipulating membrane subcompartments could be key in unravelling the biological significance of lipid domains, and could have a host of potential applications from mediating the spatial exchange of materials across lipid bilayers, to studying mobility and affinity of membrane components to lipid rafts.

Here, we demonstrate the use of light to directly trap and manipulate individual Lo domains embedded within an Ld matrix of GUVs that have been adsorbed on a glass substrate. We showcase the ability to selectively drag individual lipid domains across a membrane at will and show that the trapping laser can also be used to locally and reversibly heat the bilayer surface past Tmisc to induce domain mixing/demixing on-demand.


Optical trapping of domains

Ternary GUVs comprised of 1,2-dioleoyl-sn-glycero-3-phosphocholine (DOPC), 1,2-dipalmitoyl-sn-glycero-3-phosphocholine (DPPC) and cholesterol (2:1:1 mole ratios) were electroformed in 0.4 M sucrose in deionised (DI) water. GUVs were then added to a microscope well, and diluted 1:9 with 0.4 M glucose. Domain visualisation was achieved using fluorescence microscopy by incorporating 1 mol% Rhodamine-PE into the membrane, which partitions into the DOPC-rich disordered phases. Consistent with previous findings, we found that our GUVs were phase separated at room temperature (21 °C) with an Lo phase enriched with cholesterol and DPPC (Tm = 41 °C) and an Ld phase enriched in DOPC (Tm = −17 °C). A single-beam optical trap was coupled to a 60x 1.4 N.A. oil immersion microscope objective using custom optics and a Ytterbium fibre laser source (20 W at 1070 nm) as we have described previously13. In our setup, the position of the trap stays fixed while the motorised microscope stage is moved in two dimensions. Imaging was achieved using a CCD camera (ORCA-ER Hamamatsu) in combination with homemade LabVIEW software.

Applying the laser to a free-floating GUV had the effect of simply trapping the GUV at the laser focal point, meaning focusing and trapping individual domains was not possible. To circumvent this, we designed a system that allowed GUVs to be bound to a glass substrate. Replacing glucose with NaCl in the external solution (0.2 M) led to adhesive interactions between the glass and the membrane. This led to two observed situations41,42 (i) immobilisation, adsorption, and flatting out of the GUV on the substrate and (ii) collapse of the GUV to yield a supported lipid bilayer (SLB). The GUVs were occasionally seen to transition from the first to the second geometries, as depicted in Fig. 1a and Supplementary Movie 1. Above 0.5 mM NaCl, only the second scenario was observed. Domains in SLBs have previously been found to be affected by the underlying glass, rendering them immobile43,44. Although they mix above Tmisc, they do not macroscopically demix upon cooling due to the reduced lipid mobility43. This behaviour was seen in our system as well, and trapping of such domains was not possible with optical forces used.

Fig. 1
figure 1

Experimental setup (a) Schematic of transitions observed in the presence of 0.2 M NaCl. Adsorbed GUVs did not always transition to SLBs, and it is on these structures that domains could be manipulated. b Fluorescence images of adsorbed GUVs transitioning into SLBs. As expected, the area enclosed by fluorescence perimeter (red) increased, and the mean fluorescence intensity per unit area decreased upon SLB deposition. c Fluorescence image and schematic of Lo/Ld domain on an adsorbed GUV, with the laser (red) trapping the domain interface. Domains were manipulated at 0.23 W (at trap) laser powers. All scale bars = 10 µm

When GUVs adsorbed and did not collapse on the glass substrate however, domains remained mobile. Adsorbed GUVs adopt a flattened structure41,42 with the upper portion of the membrane unaffected by the underlying substrate. This architecture is supported by the observation that on occasions where the GUV transitioned between an adsorbed GUV and collapsed SLB, fluorescence intensity per area decreased and the area of the fluorescence patch increased, as shown in Fig. 1b. This observation suggests that the flattened GUV contains fluorescence intensity contributions from two bilayers and, hence, the objective depth of field (ca. 0.5 µm) is of the same order of the flattened GUV thickness.

The lack of interaction between the domain and the glass substrate allowed optical manipulation. Upon positioning the optical trap at the interface of the two phases and turning the power up to 0.23 W (at the trap), we found that we could trap and dynamically manipulate the position of the Lo phase in 2D by moving the microscope stage (Fig. 2a; see Supplementary Movies 2 and 3).

Fig. 2
figure 2

Optical manipulation of membrane domains (a) Fluorescence images showing side-to-side movement of a liquid ordered domain on an adsorbed GUV. Schematic showing location of laser (red) and direction of movement (arrow) is shown below. Domains are dragged by the optical traps at the interface of the two phases. b Dragging the domain by the interface leads to a slight deformation away from a spherical geometry due to drag forces. All scale bars = 10 µm

Trapping was observed reproducibly provided GUVs were adhered to the surface (i.e., not free floating) and did not rupture to yield SLB. A minimum of 15 GUVs for each composition tested was explored. Domains were dragged from the edge, not from the centre, indicating that the interface itself was being trapped, and slight deformations of the domains away from a fully spherical geometry were seen upon movement due to drag forces (Supplementary Movie 4). Domains could be manipulated to reside in different regions of the GUV (Fig. 2). It is noted that at equilibrium, as well as during manipulation, the Lo/Ld interface remained always located near the laser beam waist. This observation suggests that domain trapping and manipulation are the result of optical gradient forces, originating from the difference in both membrane refractive index and thickness between the Lo and Ld phases45,46, as opposed to laser-induced thermal effects. Indeed, it is known that membrane domains have different thicknesses, with more ordered domains tending to be thicker47,48,49. The effect of the height mismatch on trapping is a consequence of the fact that both phases have a different refractive index to the surrounding medium. Furthermore, had the domain motion been driven by a thermophoretic effect, at equilibrium the laser beam would have been located at the centre of the circular Lo domain for symmetry reasons. It was observed that the domain interface could not be trapped when the laser beam was positioned a short distance away (~μm). This is consistent with the rapid exponential decay of the optical gradient force with the distance r between the trap and the domain interface, discussed in the next section. All these observations support our interpretation of optical trapping as the driving mechanism for lipid domain manipulation. We also noted that the domain could not be manipulated in the direction parallel to the optical axis of the laser beam or outside of the GUV perimeter.

We also tried trapping gel domains in a liquid matrix in GUVs composed of DOPC/DPPC 1:1. The phase separated GUVs consisted of an interlinked mesh of gel domains, exhibiting a percolation pattern. We were not able to determine successful trapping due to their small size and difficulty in resolving their spatiotemporal positioning on the epi-fluorescent microscope.

Force balance on optically-trapped moving domain

When a lipid domain is pulled by an optical trap (Fig. 3a), the component Ftrap of the optical trapping force, parallel to the lipid bilayer, is balanced by the viscous drag Fdrag. To verify this physical description, we derive a quantitative estimate of the photonic and hydrodynamic forces under our experimental conditions and demonstrate that they are of the same magnitude. A coordinate reference system with the origin in the trap centre, as shown in Fig. 3b, is introduced. Since the beam radius ω is much smaller than the domain radius a, both ordered and disordered phases are modelled as two semi-infinite membranes with refractive indices no and nd, viscosities ηo and ηd, and thicknesses do and dd, respectively. The membranes are surrounded by an aqueous subphase and superphase of viscosity η1 and η2, respectively. The domain interface is perpendicular to the x-axis and the distance between the trap centre and the interface is denoted as r. By using the approach of Tlusty et al.50, an approximated expression of the optical trapping force Ftrap exerted by the laser on the trapped domain can be derived as

$$F_{trap} = - \frac{{\partial W}}{{\partial r}}$$


$$W = \frac{{\varepsilon _0}}{2}{\int}_{V_{obj}} {\left( {n_m^2 - n_{obj}^2} \right)\left| {\vec E} \right|^2dV}$$

is the interaction energy between the laser trap and the trapped object (i.e., the Lo and Ld phase membranes) with ε0 the vacuum permittivity, nm the refractive index of the surrounding aqueous phase, nobj and Vobj the refractive index and volume of the trapped object, respectively. \(\vec E\) is the electric field of the trapping beam, which is difficult to evaluate as it includes both the incident beam as well as the scattered field. However, due to the nanometre thickness of the membrane, the unperturbed incident field \(\vec E_0\) may be considered. For sake of simplicity, the electric field \(\vec E\) can be described by an approximated axially-symmetric Gaussian beam51

$$\left| {\vec E} \right|^2 = \frac{{4{\kern 1pt} P}}{{c{\kern 1pt} n_m{\kern 1pt} \pi {\kern 1pt} \varepsilon _0\omega ^2}}{\mathrm{exp}}\left( { - \frac{{2{\kern 1pt} \rho ^2}}{{\omega ^2}}} \right){\mathrm{exp}}\left( { - \frac{{2z^2}}{{\omega ^2\xi ^2}}} \right)$$

with P the laser power, c the speed of light, \(\rho = \sqrt {x^2 + y^2}\) the radial distance from the beam axis, z the axial distance from the trap centre, ω the beam radius and ξ the beam eccentricity50. In principle, this simplified description of the electric field is not valid for our experimental conditions since the vector character of the electromagnetic field cannot be neglected for a highly focused beam52. Nevertheless, previous studies40,50 have shown that Eq. (2) can be adopted to gain a qualitative insight on the trapping force exerted by a tightly focused laser beam. By performing the integration in Eq. (2) with nobj = nd for x < r and nobj = no for x ≥ r, it follows

$$\begin{array}{*{20}{l}} W \hfill & = \hfill & {\sqrt {\frac{\pi }{8}} \frac{{P n_m {\kern 1pt} \omega {\kern 1pt} \xi }}{c}\left[ {\left( {1 - \frac{{n_d^2}}{{n_m^2}}} \right)\left( {1 + {\mathrm{erf}}\left( {\frac{{r\sqrt 2 }}{\omega }} \right)} \right){\mathrm{erf}}\left( {\frac{{d_d }}{{\sqrt 2{\kern 1pt} \omega {\kern 1pt} \xi }}} \right) + } \right.} \hfill \\ {} \hfill & {} \hfill & {\left. { + \left( {1 - \frac{{n_o^2}}{{n_m^2}}} \right)\left( {1 - {\mathrm{erf}}\left( {\frac{{r\sqrt 2 }}{\omega }} \right)} \right){\mathrm{erf}}\left( {\frac{{d_o }}{{\sqrt 2{\kern 1pt} \omega {\kern 1pt} \xi }}} \right)} \right]} \hfill \end{array}$$

and, hence according to Eq. (1)

$$F_{trap} = \frac{{\partial W}}{{\partial r}} = f\frac{{P{\kern 1pt} n_m{\kern 1pt} \xi }}{c}{\mathrm{exp}}\left( { - \frac{{2r^2}}{{\omega ^2}}} \right)$$

with the pre-factor f given by

$$f = \left( {\frac{{n_d^2}}{{n_m^2}} - 1} \right){\mathrm{erf}}\left( {\frac{{d_d}}{{\sqrt 2 \omega \xi }}} \right) - \left( {\frac{{n_o^2}}{{n_m^2}} - 1} \right){\mathrm{erf}}\left( {\frac{{d_o}}{{\sqrt 2 \omega \xi }}} \right)$$
Fig. 3
figure 3

Estimation of force balance (a) A cylindrical lipid domain dragged at constant speed by an optical trap (b) Simplified model of the trapped object for optical force calculation, consisting of two semi-infinite domains of different thickness and refractive index

It can be seen that the peak value of the trapping force is achieved when the trap centre is located at the domain interface (i.e., r = 0). Furthermore, the pre-factor f shows that the trapping effect arises from the difference in both membrane refractive index and thickness between the Lo and Ld phases. Interestingly, the optical force may vanish if the difference in refractive index between the lipid phases (e.g., Δn = no − nd > 0) is compensated by an opposite mismatch between the phase thicknesses (i.e., Δd = do − dd < 0) so that f 0. Under the examined experimental conditions, we have ω = 300 nm, ξ = 3, P = 0.23 W and nm = 1.33. To a first approximation, we can assume that the Lo and Ld phases have refractive indices of the corresponding pure DPPC and DOPC lipid phases53, namely no = 1.4088 and nd = 1.4165. Finally, by assuming thicknesses of dd = 4.36 nm and do = 6.05 nm for the disordered and ordered phases54, respectively, Eq. (5) gives a peak value of |Ftrap|  0.4 pN.

Stone et al.55 determined the drag force exerted on a solid lipid domain of radius a bound in an infinite membrane of thickness h and viscosity η sitting between a semi-infinite inviscid fluid (superphase) and a viscous fluid (subphase) of finite depth H and viscosity η′. According to these calculations, the drag force can be expressed as

$$F_{drag}^w = 4{\kern 1pt} \pi {\kern 1pt} \eta \prime a{\kern 1pt} U{\kern 1pt} f\left( {\delta ,{\mathrm{\Lambda }}_w} \right)$$

where U is the domain velocity and f(δ, Λw) a known function of δ = H/a and Λw = ′/, which can be computed numerically55. To calculate Λw, the viscosity η of the DOPC-rich Ld phase membrane can be approximated with the viscosity of pure DOPC (0.160 Pa s at 20 °C)56. According to the numerical calculations by Stone et al.55, for a domain of radius a = 2.5 μm moving at U 2.5 μm/s, by taking h = dd = 4.57 nm, η′ = η1 = 1.5 mPas (i.e., viscosity of 0.4 M sucrose solution at 20 °C)57 and assuming δ 0.3 it results Λw 5.3 and f(0.3, 5.3)  2.7. Hence, Eq. (7) gives \(F_{drag}^w \simeq 0.3\,{\mathrm{pN}}\). It is recognised that some of the assumptions used to develop the theoretical model leading to Eq. (7) are not met under our experimental conditions, nevertheless it can be seen that the differences between the adopted theoretical description and our experimental system do not affect the magnitude of our drag force calculation. In the theoretical model55, a no-slip boundary condition between the domain and the sub-/super-phases is adopted to describe the dynamics of a solid domain. Conversely, for a liquid domain in a lipid matrix with similar viscosities, as in our experiments, an intermediate behaviour between no-slip and perfect slip (i.e., zero tangential stress) is expected. However, it is has been shown that the drag depends only weakly on the choice of boundary condition at the domain surfaces58,59 and, hence, Eq. (7) can provide a good estimate of the drag for liquid domain as well. In our flattened GUVs, the trapped Lo domains are not small compared to the Ld membrane and finite-size effects are expected to generate a drag larger than \(F_{drag}^w\), but still of the same magnitude32. Finally, in our experiments the superphase (sodium chloride solution) is not inviscid, as described in the model, but has a similar viscosity to the one of the subphase (sucrose solution). The additional drag \(F_{drag}^\infty\) caused by the semi-infinite viscous superphase can be estimated by replacing η′ = η2 = 1 mPas and δ → ∞ in Eq. (7), from which \(F_{drag}^\infty = 0.1\,{\mathrm{pN}}\), which has the same magnitude of \(F_{drag}^w\). Hence, to a first approximation the total drag exerted on a liquid domain in a flattened GUV can be estimated as \(F_{drag} = F_{drag}^w + F_{drag}^\infty \simeq 0.4\,{\mathrm{pN}}\), which, as expected, it is comparable to the optical trapping force Ftrap. This drag force estimate corresponds to a drag coefficient λ = Fdrag/U 1.6 × 10−7 N s/m. Our theoretical predictions were validated by tracking the Brownian motion of a free (i.e., not trapped) Lo domain on a Ld membrane. By analysing the domain’s mean square displacement, the domain’s diffusivity D was calculated and, hence, the corresponding drag coefficient was derived through the Einstein relation λ = kbT/D, where kb is the Boltzmann constant and T the temperature. For a domain of 2.35 µm in radius, it was measured a drag coefficient of 1.7 × 10−7 N s/m, which is of the same order of the one predicted by the model (Supplementary Fig. 1).

Laser-induced domain mixing

In addition to manipulating the Lo phase, we could also locally heat the GUV past the Tmisc (ca. 29 °C)17 and induce mixing by increasing the power of the laser source above 0.47 W at the trap (Fig. 4; Supplementary Movie 5). This leads to a temperature increase of approximately 7 °C at the laser focus (Supplementary Table 1). Domains fully mixed within 0.5 s of applying the laser, and reappeared within 0.05 s after the laser was turned off. This rapid dynamics is due to the short timescale τ = l2/α 0.2–20 ms for heat dissipation in water solution (thermal diffusivity α = 0.14 × 10−6 m2 s−1) at length scales l = 5–50 μm. Smaller circular domains were mobile, and gradually coalesced with one another until a single Lo/Ld domain remained after 24 s. The optical forces and laser powers that could be applied to the domains therefore has to be below those in which local heating leads to mixing.

Fig. 4
figure 4

Domain mixing using laser-induced heating fluorescence images showing complete domain mixing within 0.5 s of exposure to a laser. Within 0.05 s of turning the laser off, demixing is observed. Domain collision and coalescence was then observed until a single domain remains after 24 s. Scale bar = 10 µm

To demonstrate the generality of our approach we were able to achieve laser-induced phase transitions in GUVs composed of six different DOPC/DPPC/Chol lipid molar fractions, and hence different Tmisc. GUVs showing gel/liquid coexistence, as well as Lo/Ld coexistence were examined. We focussed the optical trapping laser at the GUV centre and increased the laser power at 20 mW (at trap) increments and determined at what power a threshold was reached and miscibility of the coexisting phases was observed to give a fully mixed system. We then translated these laser power values to a temperature increase through a calibration curve (Supplementary Table 1). Our results map on to the Tmisc values obtained from literature (Fig. 5)17, which validates our laser-induced heating approach. These results also indicate that lipid thermal absorption effects are not significant in this context. Control experiments with GUVs containing fully saturated DPhPC instead of unsaturated DOPC confirmed that these phase separation transitions were not due to photo-oxidation effects (Fig. 5d; Supplementary Note 1). Critically, this approach allows us to select individual vesicles in a population to undergo mixing, adding an element of spatiotemporal control compared to bulk heating approaches.

Fig. 5
figure 5

Tmisc of different GUV compositions reached via laser-induced heating (a) Graph of Tmisc reached by applying lasers of different powers vs literature Tmisc values obtained through bulk heating. These values correspond to each another, represented by the dotted line. Error bars = SD; n = 10. bd Fluorescent images of domains before, during, and after laser applied (demixed, mixed, demixed respectively). Compositions are (b) DOPC/DPPC 1:1, gel/liquid (c) DOPC/DPPC/Chol, 1:2:2, Lo/Ld domains (light-on-dark) and (d) DPhPC/DPPC/Chol, 1:1:2, Lo/Ld domains (saturated phospholipids). Scale bar = 5 µm

We found that at laser powers below the threshold where Tmisc is reached, no change in the phase state of the domain was seen, regardless of irradiation time, due to the rapid heat dissipation timescales in this regime. When irradiating an Lo  domain in a 2:1:1 DOPC/DPPC/Chol GUV for 4 min at 100 mW laser power at the trap no mixing was observed, as this was still below the laser power where a miscibility transition occurred. We measured the area of the Lo domain over time, and indeed this remained constant over the timescale of the experiments (Supplementary Fig. 2).


We show that membrane domains can be assembled, mixed, demixed and directly manipulated with spatiotemporal control using optical traps. This approach represents a significant milestone toward assembling vesicles with user-defined lateral organisation of membrane content. This is key for the design of new functional membrane-based microsystems. In addition, just as optical traps have proved instrumental in elucidating various aspects of membrane biophysics, our approach can likewise be used to study the physical and mechanical properties of lipid domains, for example by using multi-trap or holographic trapping systems to probe the energetics of domain splitting and reassembly, and by deforming domains away from spherical geometries.


Vesicle generation

All lipids were purchased from Avanti Polar Lipids (Alabaster, USA), and unless otherwise specified reagents purchased from Sigma Aldrich (Gillingham, UK). GUVs were formed via electroformation. Lipid solutions were prepared with 1 mol% Rh-PE, was first prepared by dissolving appropriate amounts of lipid in chloroform to yield 1 mg ml−1 solution. 40 µl of this solution was then spread evenly on an indium tin oxide (ITO) slide, and as the chloroform evaporated a lipid film was deposited. The slide was placed in a desiccator for a minimum of 30 min to remove residual chloroform. A 5 mm thick polydimethylsiloxane (PDMS) spacer with a central cut-out was sandwiched in between two ITO slides, one of which contained the lipid film, with the conductive sides facing each other. This chamber was held together with clips, and was filled with 0.4 M sucrose solution in DI water. An alternating electric field (1 V, 10 Hz) was applied across the ITO plates using a function generator (Aim-TTi, TG315). After two hours, the electric field was changed to 1 V, 2 Hz for a further hour, and the resulting vesicles collected. Domain trapping experiments were conducted with a DOPC/DPPC/Chol 2:1:1 (mol ratio) mixture. GUV compositions for the laser-induced miscibility experiments are given in the text.

Preparing adhered GUVs

Coverslips were first cleaned thoroughly by sonication in detergent (PCC-52, Thermo Fischer Scientific, Waltham, USA) and water for 15 min, followed by extensive rinsing in DI water, and finally by a 2-min plasma treatment (Harrick Plasma Cleaner; Ithaca, USA) to remove any residues on the glass surface. A thin PDMS spacer was used to create a well to which 45 µL of 0.2 M NaCl in DI was added. 5 µL of GUV suspension was then added, and a coverslip placed on top to seal the chamber. Domains were imaged on a Nikon Eclipse TE2000-E  under fluorescence using a mercury-fibre illuminator (Nikon Intensilight C-HGFIE), using a TRITC filter with 10 ms camera exposure.

Laser-induced domain mixing

5 µL of GUV solution containing 0.4 M sucrose was placed in a well containing 95 µL 0.4 M glucose. The well was sealed with a coverslip and the GUVs imaged in fluorescence mode (10 ms exposure TRITC filter). The laser was focussed at the GUV centre, and the power increased at 20 mW (at trap) increments until domain mixing was observed. GUVs were exposed for a maximum of 2 s at every acquisition event to minimise the effects of photo-oxidation processes. All experiments were performed at a room temperature of 21 °C. The objective transmittance and temperature increases due to the laser was quantified using a two-objective measurement method similar to the one described by Misawa et al.60 as we have adapted previously (Supplementary Table 1)15.